This work was supported by The British Heart Foundation and The Oak Foundation.

Laboratuvar Hayvanları Kullanımı ve Bakımı Kurumsal Komitesi tarafından onaylanan protokollere göre tüm hayvan deneyleri. Kültür Medya 1. Hazırlık <ol><li> F-12K ortamı,% 10 fetal sığır serumu (FBS) ve 100 U / ml penisilin ve streptomisin: insan fibroblast hücre çizgisi CCL-153 kültür ortamı olun. </li><li> PiPSC üretimi için yeniden programlanması Ortamın: Nakavt Dulbecco modifiye kartal ortamı (DMEM)% 20 Nakavt serum değiştirilmesi, 0.1 mM β-merkaptoetanol, 0.1 mM Minimum Esansiyel Medium (MEM) Aslî Olmayan Amino Asitler, 10 ng / ml temel fibroblast büyüme faktörü 2 (bFGF-2) ve 100 U / ml penisilin ve streptomisin üzerine yayıldı. Medyayı kullanmadan önce bFGF-2 taze her zaman ekleyin. </li><li> Düz kas hücresi uyarılması için Farklılaşma Ortamı (DM) olun (SMC) farklılaşması:% 10 FBS, 0.1 mM β-merkaptoetanol, 100 U / ml penisilin ve streptomisin ve 25 ng / ml Platelet Derive Büyüme Faktörü içeren medya-MEM α(PDGF-ββ). </li><li> Yap Endotel Farklılaşma Ortam endotel hücre (AK) farklılaşmasını uyarması (AT-DM): Endotel Büyüme ortamı-2 (EGM-2), 50 ng içeren ortam / ml Vasküler Endotel Büyüme Faktörü (VEGF) ve 100 U / ml penisilin ve streptomisin üzerine yayıldı. </li></ol> Kısmen kaynaklı Pluripotent Kök Hücre içine 2. yeniden programlanması İnsan Fibroblastlar (PiPSC) <ol><li> Kültür ortamı içinde,% 0.04 jelatin çözeltisi kaplamalı şişeler Kültür insan fibroblast hücre çizgisi CCL-153. </li><li> Geçiş hücreleri 1 arasında bir oranda her 3 günde bir, 6. PiPSC kuşak en yüksek verimlilik için geçit 9 önce hücrelerin kullanın. % 90 ortak akışkanlığa - Hücreler 80 ulaştıktan sonra transfeksiyon için hazırdır. </li><li> 4 yeniden programlama faktörleri içeren polisistronik plazmid pCAG2LMKOSimO linearize oktamer bağlayıcı transkripsiyon faktörü 4 (Oct4), Sox2 Kruppel benzeri faktör 4 (Klf4) ve c-myc (pCAG-OSKM). 37 ° C&#39;de 3 saat Pvu I kısıtlama enzimi 5 adet olan plazmid 5 ug Digest. Arındırmaküreticinin protokolüne göre, ticari bir kit kullanılarak plazmid. </li><li> Transfekte üreticinin protokolüne uygun olarak insan deri fibroblast (NHDF) nucleofection kiti ile elektroporasyon yoluyla doğrusallaştırılmış pCAG-OSKM plazmid 4 ug 2 x 10 6, insan fibroblast. Yavaşça önceden ısıtılmış yeniden programlanması Medya 5 ml ihtiva eden ön% 0.04 jelatin kaplı T25 şişesi üzerine transfekte edilmiş hücreleri, tohum. </li><li> 24 saat sonra, transfekte edilen hücrelerin saf popülasyonu seçmek için 25 ug / ml neomisin ve ek orta değiştirin. </li><li> 4 gün kadar her gün orta değiştirin. Not: İnsan fibroblastları yeniden programlama 4 gün sonra PiPSC olur. </li></ol> Endotel ve düz kas hücrelerinin içine PiPSC 3. Farklılaşma <ol><li> 4 gün boyunca DM içeren kolajen IV önceden kaplanmış yemekleri Tohum PiPSC SMC&#39;ler içine farklılaşmayı teşvik etmek. 4 gün kadar her gün orta değiştirin. </li><li> Kolajen IV önceden kaplanmış yemekleri c Tohum PiPSC6 gün süre ile endotelyal-DM ontaining endotel hücrelerine farklılaşmasını uyarması. 6 gün kadar her gün orta değiştirin. </li></ol> 4. decellularized Aort Greft Hazırlanması Not: Tüm çözümler ve ekipman steril olmalıdır. <ol><li> Servikal dislokasyon ile fare Kurban ve diseksiyon mikroskop altında yatar pozisyonda fare sabitleyin. </li><li> Göğüs boşluğu açmak için sternum üzerinden ve göğüs kafesi etrafında kesin. Aorta maruz kalp, akciğerler ve yemek borusu çıkarın. Yavaşça forseps ile peri-aort yağ çıkarmak. </li><li> Makasla ön ucundan aort kesin ve hafifçe künt forseps ile sona tutun. Künt diseksiyon ile arkasında omurga sütununda aort ayırın. Dikkatle bipolar elektrokoagulatör ile ligasyonu ile aort tüm dallanma arterlerin kapatın ve makas ile ligasyon uzak ucundan kesim. </li><li> 3 m ile aort lümeni temizlemek için bir 5 ml şırınga kullanınkan pıhtılarının oluşumunu önlemek için, heparin, 100 U ihtiva eden tuz çözeltisi l. </li><li> Böbrek içine şube önce aort arka ucunu kesin. Aort bütünlüğünü tutulması tüm prosedür sırasında çok önemlidir. </li><li> Fosfat tamponlu tuzlu su (PBS) içinde sulandırılmış% 0.075 sodyum dodesil sülfat (SDS) çözeltisi, 5 ml ile aort lümeni yıkayın. </li><li> 10 cm Petri kabındaki 0.075% SDS çözeltisi içinde torasik aorta bekletin. Oda sıcaklığında 150 rpm&#39;de 2 saat boyunca orbital bir karıştırıcı üzerinde Petri tabağına yerleştirin. </li><li> PBS 5 ml aort lümeni yıkayın. </li><li> 10 cm Petri için PBS içinde aort bekletin. Oda sıcaklığında 150 rpm&#39;de 2 saat boyunca orbital bir karıştırıcı üzerinde Petri tabağına yerleştirin. PBS her 20 dakikada yenileyin. </li><li> PBS 5 ml aort lümeni yıkayın. </li><li> En fazla bir hafta boyunca 4 ° C&#39;de PBS içinde hücresizleştirilmiş aort greft tutun. </li></ol> PiPSC ve Biyoreaktör Havalandırma 5. Çift Tohumculuk Not: Tüm çözüms ve ekipmanlar steril olmalıdır. Bir doku kültürü kaputu tüm işlemleri gerçekleştirin. <ol><li> Şekil 1&#39;de gösterildiği gibi. Biyoreaktör akış devreyi kurunuz boru ile kuluçka odasına, medya rezervuar, peristaltik pompa ve uyum odasını bağlayın. Dolaşımı için gerekli ortamın az hacmi 40 ml&#39;dir. </li><li> Ön-koşul, bir 10 cm Petri için DM ortamı aortu ıslatılması ile kültür ortamı ile hücresizleştirilmiş damar. Oda sıcaklığında 50 rpm&#39;de 1 saat boyunca orbital bir karıştırıcı üzerinde Petri tabağına yerleştirin. </li><li> Mikroskop altında decellularized kabın iki ucunda içine 1 cm uzunluğunda Naylon tüpleri (OD 0.9 mm, ID 0.75 mm) takın. Gemi ve 8-0 ipek dikişlerle tüpleri kravat. </li><li> Bölme duvar giriş ve çıkış portları (1/32 &quot;boru) ile Naylon tüpler bağlanarak kuluçka odasında decellularized aort greft birleştirin. Orta 5mls her seferinde inkübasyon odası koruyun. </li><li> Ekleyerek önceden ısıtılmış tarafından Trypsinize PiPSCtripsin kültür çanak kapağı ve hafifçe çanak 10 kez rock. Tripsin atın ve 2 inkübatör çanak bırakın - 3 dk. Tabak önceden ısıtılmış bir kültür ortamı ilave edin ve hücreleri ile orta karıştırın. </li><li> Hemasitometre kullanarak hücre sayısını sayın. Santrifüj 300 x g 5 dakika boyunca 5 x 10 5 hücre, her biri hücre süspansiyonları iki alikot. Tamamen süpernatant aspire. </li><li> Tamamen süpernatant aspire sonra, DM 50 ul pip hücre pelet 1 pelletini. Decellularized damar lümenine bu hücre süspansiyonu enjekte. </li><li> Ardından, Matrigel 100 ul diğer tırtıl hücre pelletini. Dikkatle decellularized aort greft üzerine karışımı pipetle. </li><li> Karışım damar dış yüzeyi etrafında sarar eşit bir jel gibi devlet dönüşür kadar 15 dakika - 10 için bekleyin. DM inkübasyon odası doldurun. </li><li> 37 ° C&#39;de bir% 5 CO2 inkübatörü içinde ayarını bütün biyoreaktör yerleştirin. Elle ilk 2 saat içinde decellularized greft boyuna ekseni her yarım saatte yaklaşık 90 ° döndürün. </li><li> Hücre yapışmasını sağlamak için 12 saat için statik kültür tutun. </li><li> Düz kas hücre değişimini etkileme peristaltik pompa ile lümen yoluyla DM verin. 5 ml / dakika ve 24 saat boyunca 20 ml / dakika için adım adım artış, başlangıç ​​akış hızını başlatın. </li><li> 24 saat süre ile 20 ml / dak dolaşım aracı, akış hızı tutun. </li><li> Orta akışını durdurun ve inkübatör dışına ayarı biyoreaktör taşımak. </li><li> Yeniden tohum PiPSC ile greft lümen. 5.6 - Trypsinize, adımlarda 5.5 olarak saymak ve santrifüj 1 x 10 6 PiPSC. 50 ng / ml VEGF ihtiva eden EGM-2 ortamında 50 ul içinde tekrar süspansiyon hücreleri. Greft lümenine hücre karışımı enjekte edilir. </li><li> Endotel değişimi etkilemek için 50 ng / ml VEGF ihtiva eden EGM-2 ortamında inkübasyon odası ve bütün dolaşımda orta değiştirin. </li><li> Inci geri ayarı biyoreaktör TaşıE inkübatör. Manuel greft ilk 2 saat içinde 90 ° her 30 dk döndürmek ve daha sonra 12 saat için statik bir kültür tutun. </li><li> 5 ml / dakika ve 35 ml / dak kadar adım adım artış, akışı dolaşan başlatın. 5 gün boyunca 35 ml / dakika akış hızındaki tutun. Her gün dolaşan ve oda ortamı değiştirin. </li><li> Fare daha fazla aşılama için tasarlanmış greft Hasat. </li></ol> Fareler içine Çift numaralı seribaşı PiPSC Graft 6. Tırnak <ol><li> Kullanım NOD.CB17-Prkdc scid / damar grefti alıcı olarak NcrCrl erkek fareler. 35 gr, ve iyi sağlık koşulları içinde - Her zaman fareler, yaklaşık 10 haftalık olan yaklaşık 25 tartmak emin olun. </li><li> Periton boşluğu içine Hypnorm (25 mg / kg) ve Hypnovel (25 mg / kg) &#39;in bir bileşimini vermek suretiyle alıcı fare anestezisi. Anestezi altında iken kuruluğu önlemek için göze vazelin oftalmik merhem sürün. Fareler rahat kasları var ve sürekli nefes sağlayarak verimli anesthetization onaylayın. <ol><li> Onun boynu tıraş ve genişletilmiş bir yatar pozisyonda fare sabitleyin. Fare solunum yolu açık kalmasını sağlamak için anestetikler ile kombinasyon halinde atropin sülfat (1,7 mg / kg) uygulayınız. </li></ol></li><li> Fare sternum alt çenenin bir orta hat kesi hazırlayın. 5- ila 10 kat büyütme ile bir mikroskop altında, yanal sağ tükürük bezleri kaldırın ve sağ karotis arter ortaya çıkarmak için doğru cleidomastoid kas çıkarın. </li><li> Yavaşça yakın ucuna doğru uzak ucundan sağ ortak karotid arteri harekete geçirmek için bağlanmış dokular çıkarın. Bir 8-0 ipek sütür ile iki kez karotis arter orta kısmını bağlayan ve iki bağları arasında teşrih. </li><li> Her gemi sonunda otoklav naylon tüp yapılmış bir manşet geçmek ve microhemostat kelepçeleri her ucunu sabitleyin. </li><li> Bir ucunda dikiş bağı sökün ve heparinin bir damla (100 U / ml) uygulanır. Hemen sonra, th uzak ucunu terse arter tüm manşet vücudu kapsayacak ve manşete bir 8-0 ipek sütür ile ters gemi düzeltmek için. <ol><li> Arterin diğer kısmına aynı işlemi tekrarlayın. Tuzlu su çözeltisi ile yıkayın arter kan pıhtıları kaldırmak için. </li></ol></li><li> Arter manşetleri aşkın decellularized damar uçlarını sürgülü ve 8-0 ipek sütür ile sabitlemek karotis arter iki ucu arasında bir decellularized damar grefti implante. Greft atışını değerlendiren önce ya biter vasküler kelepçeleri çıkartın. </li><li> Geri orijinal konumuna doğru tükürük bezi yerleştirin. 6-0 polyglactin sütür kullanarak bir kesintiye sütür ile cerrahi yere cilt kapatın. </li><li> Prosedür tamamlandıktan sonra bilincini yeniden başlayıncaya kadar tutarlı, fare hayati belirtilerini gözlemlemek. Servikal dislokasyon ve hasat damar grefti ile 24 saat ya da daha sonra daha fazla analiz için 3 hafta ya alıcı fareler Kurban. </li></ol>

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T., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Comparison+of+different+decellularization+procedures+of+porcine+heart+valves.">Comparison of different decellularization procedures of porcine heart valves.</a> Int J Artif Organs. 26 (5), 421-427 (2003).</li><li>Stephenson, E., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Derivation+and+propagation+of+human+embryonic+stem+cell+lines+from+frozen+embryos+in+an+animal+product-free+environment.">Derivation and propagation of human embryonic stem cell lines from frozen embryos in an animal product-free environment.</a> Nature Protocols. 7, 1366-1381 (2012).</li><li>Takahashi, K., Okita, K., Nakagawa, M., Yamanaka, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Induction+of+pluripotent+stem+cells+from+fibroblast+cultures.">Induction of pluripotent stem cells from fibroblast cultures.</a> Nature Protocols. 2, 3081-3089 (2007).</li><li>McCall, F. C., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Myocardial+infarction+and+intramyocardial+injection+models+in+swine.">Myocardial infarction and intramyocardial injection models in swine.</a> Nature Protocols. 7, 1479-1496 (2012).</li><li>Olausson, M., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Transplantation+of+an+allogeneic+vein+bioengineered+with+autologous+stem+cells:+a+proof-of-concept+study.">Transplantation of an allogeneic vein bioengineered with autologous stem cells: a proof-of-concept study.</a> Lancet. 380 (9838), 230-237 (2012).</li></ol>

Yazarlar herhangi çatışan mali çıkarları var.

Mevcut protokol fonksiyonel doku mühendisliği kaplar insan fibroblastlardan PiPSC kullanılarak üretilebilir olan bir ses, hızlı, basit, verimli ve tekrarlanabilir bir strateji gösterir. Bu teknik, yakın gelecekte rejeneratif tıp, doku mühendisliği ve potansiyel hastaya özgü hücre tedavisi için değerli bir araç temsil eder. Protokol etkinliğini sağlamak için kritik adım vasküler biyoreaktör içinde PiPSC hazırlanmasını, steril ve tamamen hücresizleştirilmiş aort greft, iskeleleri PiPSC başar...

vasküler kanalların yapımı kardiyovasküler hastalıklar sonucu hasar ve yaralı damarların cerrahi onarımı için bir temel stratejidir. , Alograftlarını, otolog doku (perikard veya safen ven) ve xenografts 1; Bugüne kadar, cerrahide kullanılan greft materyalleri biyouyumlu sentetik polimerler ([Gore-Tex ePTFE] veya polietilen tereftalat [Dacron] politetraflüoroetilen [Teflon], genişletilmiş politetrafloroetilen) içerir. Yapay greftler (örn, Gore-Tex ve Dacron) en sık kullanılan iken, bu malzemeler büyük olasılıkla darlık, kalsiyum birikimi, trombo-embolizasyon ve enfeksiyonlar dahil birçok kısa ve uzun vadeli komplikasyonlara neden. Ile mevcut biyolojik greft olan hastalar tromboembolik olaylar azalmış olsa da, hala bu tür kireçlenme bozulması 2 sayesinde ikincil greft yetmezliği ve kısaltılmış dayanıklılık gibi sınırlamalarla karşılaşabilirler. Bu nedenle, cerrahi t önemli gelişmelere rağmenyaş, araştırmacılar ve klinisyenler üzerinde tekniki hala damar hastalıkları için ideal bir kanal tanımlamak için ihtiyaç yükü vardır. Daha yakın zamanlarda, vasküler doku mühendisliği araştırma alanı hücreleri başarılı aşılama 1 için fonksiyonel gemi özetler bir biomimetic ortamı yaratmak amacı ile, biyolojik olarak parçalanabilen iskeleleri dahil edildiği bir kavram üretti. Temelde, vasküler yapıların başarısı üç temel bileşenleri bağlıdır; yani iskele, bir endotelyal hücre iç tabaka ve bir düz kas hücresi tabakası, ana damar karşılaştırılabilir mekanik özelliklerinin temin edilmesi için uygun olan hücre dışı matris içeren bir iskele ve / regülatör başlatılması için gerekli olan hücre / moleküler sinyali meydana getiren hücreler onarım. Uzun vadeli greft açıklığı ve neo-dokuların sürekli gelişim, inci iskelelerinin etkin hücre tohumlama son derece bağımlı olanereby kritik öneme sahip, hücre tipi kararını hale getirir. Çeşitli raporlar, küçük çaplı devreleri 3-6 geliştirmek için olgun endotelyal ve çeşitli kaynaklardan yumuşak kas hücrelerinin kullanımını göstermektedir. Umut verici olmasına rağmen, yeterli otolog damarların olmaması, olgun endotel ve düz kas hücrelerinin önemli bir yük olarak kalmaktadır elde edildi. Daha yakın zamanlarda, çeşitli kaynaklardan alınan kök hücreler vasküler doku mühendisliği uygulamaları için istismar edilmiştir. Gerçekten de, embriyonik kök hücreler 7 de dahil olmak üzere, kök hücre tipleri, çeşitli uyarılmış pluripotent kök hücreler (iPSCs) 8,9, PiPSC 10,11, kemik iliğinden türetilmiş mononükleer hücreler, 12, mezenkimal kök hücreler 13, endotelyal progenitör hücreler ve erişkin damar duvarı kök türevi hücre antijeni-1 (Sca-1) + 14,15 tanımlanmış tüm ortam yanıt olarak fonksiyonel endotel veya düz kas hücreleri ya da farklılaşma yeteneğine sahip olduğu gösterilmiştir kök / progenitör hücreleri veKültür koşulları. Ayrıca, kök hücrelerin sınırsız kendini yenileme kapasitesi onlara olgun endotel ve sadece büyüme tutuklama ve yaşlanmayı geçiren kez önce sonlu sayıda bölebilirsiniz düz kas hücrelerinin aksine daha aday olun. aşılama gibi biyouyumluluk, biyomekanik özellikleri ve biyolojik ayrışma oranı gibi çeşitli faktörlere bağlıdır için iskele malzemesinin seçimi başarılı doku mühendisliği gemi üretmek için. Temelde, malzeme biyobozunur olmalıdır greft için iskeleler oluşturmak için kullanılan ve gereksiz alıcı bağışıklık yanıtları monte olmaz. Ayrıca, hücre eki ve sonraki yaşam için uygun bir gözeneklilik ve mikro kapsaması gerekir. Bugüne kadar, vasküler doku mühendisliği iskeleleri için kullanılan en yaygın malzeme poliglikolik asit, polilaktik asit, ve poli ε-kaprolakton 16 polimerleri içerir. Daha yakın zamanlarda, decellularized biyolojik maddeler varAyrıca bazı başarı ile uygulanmıştır. Çeşitli laboratuarlar otolog hücreler hücresizleştirilmiş bir insan, köpek veya domuz damarları tohumlama pıhtılaşma ve intimal hiperplazi 17-19 karşı biyolojik bir greft mesafede olduğunu göstermiştir. Vasküler doku mühendisliğinde diğer stratejiler iskele desteği 20, 21 olmadan örneğin hücre dışı matriks proteinleri tabanlı vasküler greft, fibrin jel 13 tohumlama hücreleri ve üreten hücre tabakaları içerir. Mevcut protokol fonksiyonel endotel ve düz kas hücreleri, ağır kombine immün yetmezlik içine doku mühendisliği gemilerin fonksiyonel PiPSC türetilmiş damar hücrelerini liman için decellularized damar iskele oluşan biyoreaktör ve grefti nesil (SCID içine insan PiPSC farklılaşmasını gösteriyor ) fareler. PiPSC bu hücreler farelerde tümörler oluşturur ya da etik zam yok, çünkü damar greft doku mühendisliği için kullanılacak optimum hücre tipi veallo-immün yanıtlar. Ayrıca, biz pip-endotel hücreleri ve tırtıl-düz kas hücrelerinin üretilmesi için strateji verimli ve 10,11 tekrarlanabilir olduğunu göstermiştir. Bundan sonra, biz, böylece aşılama ve hayatta kalma etkinliğini arttırmak, yakından bir yerli geminin içinde var matriks proteinleri taklit etmek PiPSC türetilmiş vasküler hücrelerin tohumlama için bir decellularized gemi tasarladı. Bundan başka, tohumlama PiPSC damarların decellularization makrofajlar gibi bağışıklık hücre tipleri ile monte enflamatuar yanıtların ortaya çıkmasını engellemektedir. Daha da önemlisi, bu protokol sadece insanlar içine çeviri için damar olukları umut oluşturmak için bir metodoloji temsil etmez, aynı zamanda eğitim ve fare modelleri ile vasküler doku yenilenmesini yöneten moleküler mekanizmaları anlamak değerli bir araç sağlar.

<table border="0" cellpadding="0" cellspacing="0" >
	<tbody>
		<tr >
			<td >Human Fibroblasts CCL-153</td>
			<td >ATCC</td>
			<td >CCL-153</td>
			<td>Prenatal human embryonic fibroblasts</td>
		</tr>
		<tr >
			<td >ATCC F-12K Medium (Kaighn&#39;s Modification of Ham&#39;s F-12 Medium)</td>
			<td >ATCC</td>
			<td >30-2004</td>
			<td></td>
		</tr>
		<tr >
			<td >Fetal Bovine Serum</td>
			<td >ATCC</td>
			<td >30-2020</td>
			<td></td>
		</tr>
		<tr >
			<td >Knockout DMEM medium optimized for embryonic stem cells</td>
			<td >Life technologies (Gibco)</td>
			<td >12660-012</td>
			<td></td>
		</tr>
		<tr >
			<td >Knockout Serum Replacement</td>
			<td >Life technologies (Invitrogen)</td>
			<td >10828-028</td>
			<td></td>
		</tr>
		<tr >
			<td >Human Basic FGF-2&#160;</td>
			<td >Miltenyi Biotech</td>
			<td >130-093-837</td>
			<td></td>
		</tr>
		<tr >
			<td >alpha-MEM medium</td>
			<td >Life technologies (Invitrogen)</td>
			<td >32571093</td>
			<td></td>
		</tr>
		<tr >
			<td >Human PDGF</td>
			<td >R&#38;D System</td>
			<td >120-HD-001</td>
			<td></td>
		</tr>
		<tr >
			<td >Gelatin Solution 2%</td>
			<td >Sigma</td>
			<td >G1393</td>
			<td></td>
		</tr>
		<tr >
			<td >Plasmid 20866: pCAG2LMKOSimO (SOX2, OCT4, KLF4, C-MYC)</td>
			<td >Addgene</td>
			<td >20866</td>
			<td></td>
		</tr>
		<tr >
			<td >&#160;PvuI Restriction Enzyme</td>
			<td >New England Biolabs</td>
			<td >RO150S</td>
			<td></td>
		</tr>
		<tr >
			<td >SureClean Plus</td>
			<td >Bioline</td>
			<td >BIO-37047</td>
			<td></td>
		</tr>
		<tr >
			<td >Nucelofection Kit (NHDF Kit)</td>
			<td >LONZA</td>
			<td >VPD-1001</td>
			<td></td>
		</tr>
		<tr >
			<td >Neomycin</td>
			<td >SIGMA</td>
			<td >G418</td>
			<td>Selection of&#160;</td>
		</tr>
		<tr >
			<td >KL 1500 LCD, Illumination for Stereo Microscopy</td>
			<td >SCHOTT</td>
			<td >KL 1500 LCD</td>
			<td>Cold light illumination for stereo microscopy</td>
		</tr>
		<tr >
			<td >Nikon Zoom Steromicroscope SMZ800</td>
			<td >Nikon</td>
			<td >SMZ800</td>
			<td></td>
		</tr>
		<tr >
			<td >Heparin sodium salt</td>
			<td >Sigma</td>
			<td >H3393</td>
			<td></td>
		</tr>
		<tr >
			<td >10% SDS Stock Solution Molecular Biology Reagent</td>
			<td >Severn Biotech</td>
			<td >CAS 151-21-3</td>
			<td></td>
		</tr>
		<tr >
			<td >Dulbecco&#39;s Phosphate Buffered Saline</td>
			<td >Sigma</td>
			<td >D8537</td>
			<td></td>
		</tr>
		<tr >
			<td >Matrigel (10mg/ml)</td>
			<td >BD</td>
			<td >A6661</td>
			<td></td>
		</tr>
		<tr >
			<td >Shaker IKA Vibrax with Shaking platform VX 7&#160;</td>
			<td >Jepson Bolton&#39;s, Janke&#38;Kunkel</td>
			<td >S32-102</td>
			<td></td>
		</tr>
		<tr >
			<td >Masterflex L/S Digital Pump Drive</td>
			<td >Cole-Parmer</td>
			<td >WZ-07523-80</td>
			<td></td>
		</tr>
		<tr >
			<td >Masterflex L/S 6-channel, 6-roller cartridge pump head</td>
			<td >Cole-Parmer</td>
			<td >EW-07519-15</td>
			<td></td>
		</tr>
		<tr >
			<td >Masterflex L/S large cartridges for pump head</td>
			<td >Cole-Parmer</td>
			<td >EW-07519-75</td>
			<td></td>
		</tr>
		<tr >
			<td >Masterflex platinum-cured silicone pump tubing, L/S 14, 25 ft</td>
			<td >Cole-Parmer&#160;</td>
			<td >WZ-96410-14</td>
			<td >Tubing goes through the peristaltic pump</td>
		</tr>
		<tr >
			<td >0.5mm ID, 0.8 mm OD Silicone Tubing</td>
			<td >SILEX</td>
			<td >N/A</td>
			<td>Tubings connect incubation chamber, media reservoir and compliance chamber&#160;</td>
		</tr>
		<tr >
			<td >Fitting Reducer 0.5 to 1.6, natural Polypropyline</td>
			<td >Ibidi</td>
			<td >10829</td>
			<td>Adapter connect above two types of tubings</td>
		</tr>
		<tr >
			<td >1/32&#34; Tubing, ID 0.01&#34; (250&#181;m) Material: PEEK</td>
			<td >LabSmith</td>
			<td >T-132-010P</td>
			<td>Tubing through the incubation chamber wall which connects the graft with outside tubing</td>
		</tr>
		<tr >
			<td >One-Piece Fittings&#160;</td>
			<td >LabSmith</td>
			<td >T-132-100</td>
			<td>Fix the above tubings through the incubation chamber wall</td>
		</tr>
		<tr >
			<td >Nylon tubes (OD 0.9mm, ID 0.75mm)&#160;</td>
			<td >Smiths Medical</td>
			<td >N/A</td>
			<td>Tubings insert into two ends of the aorta graft</td>
		</tr>
		<tr >
			<td >NOD.CB17-Prkdcscid/NcrCrl mouse</td>
			<td >Charles River</td>
			<td ></td>
			<td ></td>
		</tr>
		<tr >
			<td >Surgical sutures, 8-0&#160; silk</td>
			<td >ETHICON</td>
			<td >W819</td>
			<td ></td>
		</tr>
		<tr >
			<td >Hypnorm</td>
			<td >Vetapharm</td>
			<td >Vm21757/4000</td>
			<td >Neuroleptanalgesic for use in mice</td>
		</tr>
		<tr >
			<td >Hypnovel (Midazolam)</td>
			<td >Roche</td>
			<td >59467-70-8</td>
			<td >Induction of anaesthesia</td>
		</tr>
		<tr >
			<td >Dissecting microscope</td>
			<td >Carl Zeiss</td>
			<td >Stemi 2000</td>
			<td ></td>
		</tr>
		<tr >
			<td >Nylon Tubing</td>
			<td >Portex LTD</td>
			<td >800/200/100/200</td>
			<td >0.65 mm in diameter and 1 mm in length; to make artery cuff</td>
		</tr>
		<tr >
			<td >Electrocoagulator</td>
			<td >Martin&#160;</td>
			<td >SN 54.131</td>
			<td >Ligation of artery branches on aorta</td>
		</tr>
		<tr >
			<td >Bipolar micro hemostat forceps</td>
			<td >Martin</td>
			<td >80-91-12-04</td>
			<td >Fixation of vessel ends</td>
		</tr>
		<tr >
			<td >Vessel Dilator</td>
			<td >S&#38;T</td>
			<td >JFX-7</td>
			<td ></td>
		</tr>
		<tr >
			<td >Vessel Dilator</td>
			<td >S&#38;T</td>
			<td >JFL-3dZ</td>
			<td ></td>
		</tr>
		<tr >
			<td >Vessel Dilator</td>
			<td >S&#38;T</td>
			<td >D-5aZ</td>
			<td ></td>
		</tr>
		<tr >
			<td >Mini applier&#160;</td>
			<td >AESCULAP</td>
			<td >FE572K</td>
			<td ></td>
		</tr>
		<tr >
			<td >Micro hemostats clips</td>
			<td >AESCULAP</td>
			<td >FE720K</td>
			<td ></td>
		</tr>
		<tr >
			<td >Surgical sutures, 6-0 VICRYL</td>
			<td >ETHICON</td>
			<td >V489</td>
			<td ></td>
		</tr>
	</tbody>
</table>

generation and grafting of tissue-engineered vessels in a mouse model

The construction of vascular conduits is a fundamental strategy for surgical repair of damaged and injured vessels resulting from cardiovascular diseases. The current protocol presents an efficient and reproducible strategy in which functional tissue engineered vessel grafts can be generated using partially induced pluripotent stem cell (PiPSC) from human fibroblasts. We designed a decellularized vessel scaffold bioreactor, which closely mimics the matrix protein structure and blood flow that exists within a native vessel, for seeding of PiPSC-endothelial cells or smooth muscle cells prior to grafting into mice. This approach was demonstrated to be advantageous because immune-deficient mice engrafted with the PiPSC-derived grafts presented with markedly increased survival rate 3 weeks after surgery. This protocol represents a valuable tool for regenerative medicine, tissue engineering and potentially patient-specific cell-therapy in the near future.

PiPSC başarılı üretimi 4 transkripsiyon faktörleri, Oct4, Sox2, Klf4 ve c-myc (OSKM) taşıyan bir doğrusallaştırılmış pCAG2LMKOSimO plazmitle insan fibroblastları nucleofecting 4 gün sonra doğrulanmıştır. PiPSC fibroblastlar (Şekil 2A) ile karşılaştırıldığında belirgin bir şekilde farklı bir fenotipini gösterdi ve mRNA (Şekil 2B) ve protein (Şekil 2C) seviyelerinin 10 4 yeniden programlama faktörleri olarak ifade edilmiştir. ...

Watch this Scientific Journal Video about Generation and Grafting of Tissue-engineered Vessels in a Mouse Model at JoVE.com

Generation and Grafting of Tissue-engineered Vessels in a Mouse Model

Burada, biz çift tohumlama kısmen uyarılmış pluripotent kök hücre ile farelere aşılama için fonksiyonel doku mühendisliği gemi greft oluşturmak için bir protokol mevcut (PiPSC) - Bir decellularized damar iskele biyoreaktör üzerinde elde edilen endotel hücreleri - düz kas hücreleri ve PiPSC türetilmiş.

Bir Fare Modeli Doku mühendisliği Kapların Üretimi ve Tırnak

The construction of vascular conduits is a fundamental strategy for surgical repair of damaged and injured vessels resulting from cardiovascular diseases. ...

generation-and-grafting-of-tissue-engineered-vessels-in-a-mouse-model

Research

JoVE Journal

Bioengineering

11.9K Görüntüleme.  King's College London BHF Centre.  Burada, biz çift tohumlama kısmen uyarılmış pluripotent kök hücre ile farelere aşılama için fonksiyonel doku mühendisliği gemi greft oluşturmak için bir protokol mevcut (PiPSC) - Bir decellularized damar iskele biyoreaktör üzerinde elde edilen endotel hücreleri - düz kas hücreleri ve PiPSC türetilmiş. 

Video: Generation and Grafting of Tissue-engineered Vessels in a Mouse Model

Protocol for Relative Hydrodynamic Assessment of Tri-leaflet Polymer Valves

Limitations of currently available prosthetic valves, xenografts, and homografts have prompted a recent resurgence of developments in the area of tri-leaflet polymer valve prostheses. However, identification of a protocol for initial assessment of polymer valve hydrodynamic functionality is paramount during the early stages of the design process. Traditional in vitro pulse duplicator systems are not configured to accommodate flexible tri-leaflet materials; in addition, assessment of polymer valve functionality needs to be made in a relative context to native and prosthetic heart valves under identical test conditions so that variability in measurements from different instruments can be avoided. Accordingly, we conducted hydrodynamic assessment of i) native (n = 4, mean diameter, D = 20 mm), ii) bi-leaflet mechanical (n= 2, D = 23 mm) and iii) polymer valves (n = 5, D = 22 mm) via the use of a commercially available pulse duplicator system (ViVitro Labs Inc, Victoria, BC) that was modified to accommodate tri-leaflet valve geometries. Tri-leaflet silicone valves developed at the University of Florida comprised the polymer valve group. A mixture in the ratio of 35:65 glycerin to water was used to mimic blood physical properties. Instantaneous flow rate was measured at the interface of the left ventricle and aortic units while pressure was recorded at the ventricular and aortic positions. Bi-leaflet and native valve data from the literature was used to validate flow and pressure readings. The following hydrodynamic metrics were reported: forward flow pressure drop, aortic root mean square forward flow rate, aortic closing, leakage&#160;and regurgitant volume, transaortic closing, leakage, and total energy losses. Representative results indicated that hydrodynamic metrics from the three valve groups could be successfully obtained by incorporating a custom-built assembly into a commercially available pulse duplicator system and subsequently, objectively compared to provide insights on functional aspects of polymer valve design.

There has been renewed interest in developing polymer valves. Here, the objectives are to demonstrate the feasibility of modifying a commercial pulse duplicator to accommodate tri-leaflet geometries and to define a protocol to present polymer valve hydrodynamic data in comparison to native and prosthetic valve data collected under near-identical conditions.

Tri-broşür Polimer Vanalar göreceli hidrodinamik Değerlendirme Protokolü

Limitations of currently available prosthetic valves, xenografts, and homografts have prompted a recent resurgence of developments in the area of ...

Biyomühendislik

Preparation of Light-responsive Membranes by a Combined Surface Grafting and Postmodification Process

In order to modify the surface tension of commercial available track-edged polymer membranes, a procedure of surface-initiated polymerization is presented. The polymerization from the membrane surface is induced by plasma treatment of the membrane, followed by reacting the membrane surface with a methanolic solution of 2-hydroxyethyl methacrylate (HEMA). Special attention is given to the process parameters for the plasma treatment prior to the polymerization on the surface. For example, the influence of the plasma-treatment on different types of membranes (e.g.&#160;polyester, polycarbonate, polyvinylidene fluoride) is studied. Furthermore, the time-dependent stability of the surface-grafted membranes is shown by contact angle measurements. When grafting poly(2-hydroxyethyl methacrylate) (PHEMA) in this way, the surface can be further modified by esterification of the alcohol moiety of the polymer with a carboxylic acid function of the desired substance. These reactions can therefore be used for the functionalization of the membrane surface. For example, the surface tension of the membrane can be changed or a desired functionality as the presented light-responsiveness can be inserted. This is demonstrated by reacting PHEMA with a carboxylic acid functionalized spirobenzopyran unit which leads to a light-responsive membrane. The choice of solvent plays a major role in the postmodification step and is discussed in more detail in this paper. The permeability measurements of such functionalized membranes are performed using a Franz cell with an external light source. By changing the wavelength of the light from the visible to the UV-range, a change of permeability of aqueous caffeine solutions is observed.

A plasma-induced polymerization procedure is described for the surface-initiated polymerization on polymer membranes. Further postmodification of the grafted polymer with photochromic substances is presented with a protocol of conducting permeability measurements of light-responsive membranes.

Bir Kombine Yüzey Tırnak ve Postmodification Süreci Işık duyarlı Membranların Hazırlanması

In order to modify the surface tension of commercial available track-edged polymer membranes, a procedure of surface-initiated polymerization is ...

Surgical Technique for the Implantation of Tissue Engineered Vascular Grafts and Subsequent In Vivo Monitoring

The development of Tissue Engineered Vessels (TEVs) is advanced by the ability to routinely and effectively implant TEVs (4-5 mm in diameter) into a large animal model. A step by-step protocol for inter-positional placement of the TEV and real-time digital assessment of the TEV and native carotid arteries is described here. In vivo monitoring is made possible by the implantation of flow probes, catheters and ultrasonic crystals (capable of recording dynamic diameter changes of implanted TEVs and native carotid arteries) at the time of surgery. Once implanted, researchers can calculate arterial blood flow patterns, invasive blood pressure and artery diameter yielding parameters such as pulse wave velocity, augmentation index, pulse pressures and compliance. Data acquisition is accomplished using a single computer program for analysis throughout the duration of the experiment. Such invaluable data provides insight into TEV matrix remodeling, its resemblance to native/sham controls and overall TEV performance in vivo.

Surgical Technique for the Implantation of Tissue Engineered Vascular Grafts and Subsequent In Vivo Monitoring

A step-by-step protocol for the inter-positional placement of Tissue Engineered Vessels (TEVs) into the carotid artery of a sheep using end-to-end anastomosis and real-time digital assessment in vivo until animal sacrifice.

Doku Engineered Vasküler Greftlerinin ve sonraki İmplantasyonunda Cerrahi Tekniği<em&gt; İn Vivo</em&gt; İzleme

The development of Tissue Engineered Vessels (TEVs) is advanced by the ability to routinely and effectively implant TEVs (4-5 mm in diameter) into a large ...

Generation of a Three-dimensional Full Thickness Skin Equivalent and Automated Wounding

In vitro models are a cost effective and ethical alternative to study cutaneous wound healing processes. Moreover, by using human cells, these models reflect the human wound situation better than animal models. Although two-dimensional models are widely used to investigate processes such as cellular migration and proliferation, models that are more complex are required to gain a deeper knowledge about wound healing. Besides a suitable model system, the generation of precise and reproducible wounds is crucial to ensure comparable results between different test runs. In this study, the generation of a three-dimensional full thickness skin equivalent to study wound healing is shown. The dermal part of the models is comprised of human dermal fibroblast embedded in a rat-tail collagen type I hydrogel. Following the inoculation with human epidermal keratinocytes and consequent culture at the air-liquid interface, a multilayered epidermis is formed on top of the models. To study the wound healing process, we additionally developed an automated wounding device, which generates standardized wounds in a sterile atmosphere.

The goal of this protocol is to build up a three-dimensional full thickness skin equivalent, which resembles natural skin. With a specifically constructed automated wounding device, precise and reproducible wounds can be generated under maintenance of sterility.

Üç-boyutlu Tam Kalınlığı Deri Üretimi Eşdeğer ve Otomatik Yaralama

In vitro models are a cost effective and ethical alternative to study cutaneous wound healing processes. Moreover, by using human cells, these models ...

Production, Characterization and Potential Uses of a 3D Tissue-engineered Human Esophageal Mucosal Model

The incidence of both esophageal adenocarcinoma and its precursor, Barrett&#8217;s Metaplasia, are rising rapidly in the western world. Furthermore esophageal adenocarcinoma generally has a poor prognosis, with little improvement in survival rates in recent years. These are difficult conditions to study and there has been a lack of suitable experimental platforms to investigate disorders of the esophageal mucosa.
A model of the human esophageal mucosa has been developed in the MacNeil laboratory which, unlike conventional 2D cell culture systems, recapitulates the cell-cell and cell-matrix interactions present in vivo and produces a mature, stratified epithelium similar to that of the normal human esophagus. Briefly, the model utilizes non-transformed normal primary human esophageal fibroblasts and epithelial cells grown within a porcine-derived acellular esophageal scaffold. Immunohistochemical characterization of this model by CK4, CK14, Ki67 and involucrin staining demonstrates appropriate recapitulation of the histology of the normal human esophageal mucosa.
This model provides a robust, biologically relevant experimental model of the human esophageal mucosa. It can easily be manipulated to investigate a number of research questions including the effectiveness of pharmacological agents and the impact of exposure to environmental factors such as alcohol, toxins, high temperature or gastro-esophageal refluxate components. The model also facilitates extended culture periods not achievable with conventional 2D cell culture, enabling, inter alia, the study of the impact of repeated exposure of a mature epithelium to the agent of interest for up to 20 days. Furthermore, a variety of cell lines, such as those derived from esophageal tumors or Barrett&#8217;s Metaplasia, can be incorporated into the model to investigate processes such as tumor invasion and drug responsiveness in a more biologically relevant environment.

This manuscript describes the production, characterization and potential uses of a tissue engineered 3D esophageal construct prepared from normal primary human esophageal fibroblast and squamous epithelial cells seeded within a de-cellularized porcine scaffold. The results demonstrate the formation of a mature stratified epithelium similar to the normal human esophagus.

3D Doku mühendisliği İnsan Özofagus Mukozal Modeli Üretimi, Karakterizasyonu ve Potansiyel Kullanımları

The incidence of both esophageal adenocarcinoma and its precursor, Barrett&#8217;s Metaplasia, are rising rapidly in the western world. Furthermore ...

A Combined 3D Tissue Engineered In Vitro/In Silico Lung Tumor Model for Predicting Drug Effectiveness in Specific Mutational Backgrounds

In the present study, we combined an in vitro 3D lung tumor model with an in silico model to optimize predictions of drug response based on a specific mutational background. The model is generated on a decellularized porcine scaffold that reproduces tissue-specific characteristics regarding extracellular matrix composition and architecture including the basement membrane. We standardized a protocol that allows artificial tumor tissue generation within 14 days including three days of drug treatment. Our article provides several detailed descriptions of 3D read-out screening techniques like the determination of the proliferation index Ki67 staining&#39;s, apoptosis from supernatants by M30-ELISA and assessment of epithelial to mesenchymal transition (EMT), which are helpful tools for evaluating the effectiveness of therapeutic compounds. We could show compared to 2D culture a reduction of proliferation in our 3D tumor model that is related to the clinical situation. Despite of this lower proliferation, the model predicted EGFR-targeted drug responses correctly according to the biomarker status as shown by comparison of the lung carcinoma cell lines HCC827 (EGFR -mutated, KRAS wild-type) and A549 (EGFR wild-type, KRAS-mutated) treated with the tyrosine-kinase inhibitor (TKI) gefitinib. To investigate drug responses of more advanced tumor cells, we induced EMT by long-term treatment with TGF-beta-1 as assessed by vimentin/pan-cytokeratin immunofluorescence staining. A flow-bioreactor was employed to adjust culture to physiological conditions, which improved tissue generation. Furthermore, we show the integration of drug responses upon gefitinib treatment or TGF-beta-1 stimulation - apoptosis, proliferation index and EMT - into a Boolean in silico model. Additionally, we explain how drug responses of tumor cells with a specific mutational background and counterstrategies against resistance can be predicted. We are confident that our 3D in vitro approach especially with its in silico expansion provides an additional value for preclinical drug testing in more realistic conditions than in 2D cell culture.

A Combined 3D Tissue Engineered In Vitro/In Silico Lung Tumor Model for Predicting Drug Effectiveness in Specific Mutational Backgrounds

We present a three-dimensional (3D) lung cancer model based on a biological collagen scaffold to study sensitivity towards non-small-cell-lung-cancer-(NSCLC)-targeted therapies. We demonstrate different read-out techniques to determine the proliferation index, apoptosis and epithelial-mesenchymal transition (EMT) status. Collected data are integrated into an in silico model for prediction of drug sensitivity.

Kombine bir 3D doku mühendisliği<em&gt; İn Vitro</em&gt; /<em&gt; Siliko</emSpesifik mutasyonel Arka İlaç Etkinliği tahmin için&gt; Akciğer Tümör Modeli

In the present study, we combined an in vitro 3D lung tumor model with an in silico model to optimize predictions of drug response based on a specific ...

Applications of In Vivo Functional Testing of the Rat Tibialis Anterior for Evaluating Tissue Engineered Skeletal Muscle Repair

Despite the regenerative capacity of skeletal muscle, permanent functional and/or cosmetic deficits (e.g., volumetric muscle loss (VML) resulting from traumatic injury, disease and various congenital, genetic and acquired conditions are quite common. Tissue engineering and regenerative medicine technologies have enormous potential to provide a therapeutic solution. However, utilization of biologically relevant animal models in combination with longitudinal assessments of pertinent functional measures are critical to the development of improved regenerative therapeutics for treatment of VML-like injuries. In that regard, a commercial muscle lever system can be used to measure length, tension, force and velocity parameters in skeletal muscle. We used this system, in conjunction with a high power, bi-phase stimulator, to measure in vivo force production in response to activation of the anterior crural compartment of the rat hindlimb. We have previously used this equipment to assess the functional impact of VML injury on the tibialis anterior (TA) muscle, as well as the extent of functional recovery following treatment of the injured TA muscle with our tissue engineered muscle repair (TEMR) technology. For such studies, the left foot of an anaesthetized rat is securely anchored to a footplate linked to a servomotor, and the common peroneal nerve is stimulated by two percutaneous needle electrodes to elicit muscle contraction and dorsiflexion of the foot. The peroneal nerve stimulation-induced muscle contraction is measured over a range of stimulation frequencies (1-200 Hz), to ensure an eventual plateau in force production that allows for an accurate determination of peak tetanic force. In addition to evaluation of the extent of VML injury as well as the degree of functional recovery following treatment, this methodology can be easily applied to study diverse aspects of muscle physiology and pathophysiology. Such an approach should assist with the more rational development of improved therapeutics for muscle repair and regeneration.

Applications of In Vivo Functional Testing of the Rat Tibialis Anterior for Evaluating Tissue Engineered Skeletal Muscle Repair

We describe an in vivo protocol to measure dorsiflexion of the foot following stimulation of the peroneal nerve and contraction of the anterior crural compartment of the rat hindlimb. Such measurements are an indispensable translational tool for evaluating skeletal muscle pathology and tissue engineering approaches to muscle repair and regeneration.

Uygulamaları<em&gt; İn Vivo</em&gt; Doku değerlendirilmesi için Rat Tibialis Anterior Fonksiyonel Test İskelet Kası Onarım Engineered

Despite the regenerative capacity of skeletal muscle, permanent functional and/or cosmetic deficits (e.g., volumetric muscle loss (VML) resulting from ...

Three-dimensional Tissue Engineered Aligned Astrocyte Networks to Recapitulate Developmental Mechanisms and Facilitate Nervous System Regeneration

Neurotrauma and neurodegenerative disease often result in lasting neurological deficits due to the limited capacity of the central nervous system (CNS) to replace lost neurons and regenerate axonal pathways. However, during nervous system development, neuronal migration and axonal extension often occur along pathways formed by other cells, referred to as &#34;living scaffolds&#34;. Seeking to emulate these mechanisms and to design a strategy that circumvents the inhibitory environment of the CNS, this manuscript presents a protocol to fabricate tissue engineered astrocyte-based &#34;living scaffolds&#34;. To create these constructs, we employed a novel biomaterial encasement scheme to induce astrocytes to self-assemble into dense three-dimensional bundles of bipolar longitudinally-aligned somata and processes. First, hollow hydrogel micro-columns were assembled, and the inner lumen was coated with collagen extracellular-matrix. Dissociated cerebral cortical astrocytes were then delivered into the lumen of the cylindrical micro-column and, at a critical inner diameter of &#60;350 &#181;m, spontaneously self-aligned and contracted to produce long fiber-like cables consisting of dense bundles of astrocyte processes and collagen fibrils measuring &#60;150 &#181;m in diameter yet extending several cm in length. These engineered living scaffolds exhibited &#62;97% cell viability and were virtually exclusively comprised of astrocytes expressing a combination of the intermediate filament proteins glial-fibrillary acidic protein (GFAP), vimentin, and nestin. These aligned astrocyte networks were found to provide a permissive substrate for neuronal attachment and aligned neurite extension. Moreover, these constructs maintain integrity and alignment when extracted from the hydrogel encasement, making them suitable for CNS implantation. These preformed constructs structurally emulate key cytoarchitectural elements of naturally occurring glial-based &#34;living scaffolds&#34; in vivo. As such, these engineered living scaffolds may serve as test-beds to study neurodevelopmental mechanisms in vitro or facilitate neuroregeneration by directing neuronal migration and/or axonal pathfinding following CNS degeneration in vivo.

We showcase the development of self-assembled, three-dimensional bundles of longitudinally aligned astrocytic somata and processes within a novel biomaterial encasement. These engineered &#34;living scaffolds&#34;, exhibiting micron-scale diameter yet extending centimeters in length, may serve as test-beds to study neurodevelopmental mechanisms or facilitate neuroregeneration by directing neuronal migration and/or axonal pathfinding.

Astrocyte ağlar gelişimsel mekanizmaları özetlemek ve sinir sistemi yeniden oluşturma işlemi kolaylaştırmak için tasarlanmış üç boyutlu doku uyumlu

Neurotrauma and neurodegenerative disease often result in lasting neurological deficits due to the limited capacity of the central nervous system (CNS) to ...

A Novel Tenorrhaphy Suture Technique with Tissue Engineered Collagen Graft to Repair Large Tendon Defects

Surgical management of large tendon defects with tendon grafts is challenging, as there are a finite number of sites where donors can be readily identified and used. Currently, this gap is filled with tendon auto-, allo-, xeno-, or artificial grafts, but clinical methods to secure them are not necessarily translatable to animals because of the scale. In order to evaluate new biomaterials or study a tendon graft made up of collagen type 1, we have developed a modified suture technique to help maintain the engineered tendon in alignment with the tendon ends. Mechanical properties of these grafts are inferior to the native tendon. To incorporate engineered tendon into clinically relevant models of loaded repair, a strategy was adopted to offload the tissue engineered tendon graft and allow for the maturation and integration of the engineered tendon in vivo until a mechanically sound neo-tendon was formed. We describe this technique using incorporation of the collagen type 1 tissue engineered tendon construct.

In this paper, we present an in vitro and in situ protocol to repair a tendon gap of up to 1.5 cm by filling it with engineered collagen graft. This was performed by developing a modified suture technique to take the mechanical load until the graft matures into the host tissue.

Büyük Tendon Kusurlarını Onarmak İçin Doku Mühendisliği Kollajen Greftli Yeni Bir Tenorhaphy Dikiş Tekniği

Surgical management of large tendon defects with tendon grafts is challenging, as there are a finite number of sites where donors can be readily ...

Seeding and Implantation of a Biosynthetic Tissue-engineered Tracheal Graft in a Mouse Model

Treatment options for congenital or secondary long segment tracheal defects have historically been limited due to an inability to replace functional tissue. Tissue engineering holds great promise as a potential solution with its ability to integrate cells and signaling molecules into a 3-dimensional scaffold. Recent work with tissue engineered tracheal grafts (TETGs) has seen some success but their translation has been limited by graft stenosis, graft collapse, and delayed epithelialization. In order to investigate the mechanisms driving these issues, we have developed a mouse model for tissue engineered tracheal graft implantation. TETGs were constructed using electrospun polymers polyethylene terephthalate (PET) and polyurethane (PU) in a mixture of PET and PU (20:80 percent weight). Scaffolds were then seeded using bone marrow mononuclear cells isolated from 6-8 week-old C57BL/6 mice by gradient centrifugation. Ten million cells per graft were seeded onto the lumen of the scaffold and allowed to incubate overnight before implantation between the third and seventh tracheal rings. These grafts were able to recapitulate the findings of stenosis and delayed epithelialization as demonstrated by histological analysis and lack of Keratin 5 and Keratin 14 basal epithelial cells on immunofluorescence. This model will serve as a tool for investigating cellular and molecular mechanisms involved in host remodeling.

Graft stenosis poses a critical obstacle in tissue engineered airway replacement. To investigate cellular mechanisms underlying stenosis, we utilize a murine model of tissue engineered tracheal replacement with seeded bone marrow mononuclear cells (BM-MNC). Here, we detail our protocol, including scaffold manufacturing, BM-MNC isolation, graft seeding, and implantation.

Tohum ve bir biyosentetik doku Mühendisliği trakeal greft bir fare modeli implantasyonu

Treatment options for congenital or secondary long segment tracheal defects have historically been limited due to an inability to replace functional ...